Knee joint prosthesis and tibial component and femoral component thereof

ABSTRACT

A knee joint prosthesis and a tibial component thereof and a femoral component thereof are disclosed. The knee joint prosthesis includes a tibial component and a femoral component. The tibial component has a top surface, a bottom surface opposite the top surface and a first slot passing through the top surface and the bottom surface for accommodating a cruciate ligament. The tibial component has at least one first protrusion disposed on the bottom surface, and the first protrusion has a plurality of first through holes. The femoral component is carried by the tibial component and has a second slot for accommodating the cruciate ligament. The femoral component has at least one second protrusion disposed on a surface thereof against the tibial component, and the second protrusion has a plurality of second through holes.

CROSS REFERENCE TO RELATED APPLICATIONS

This Non-provisional application claims priority under 35 U.S.C. §119(a)on Taiwan Patent Application No(s). 104105153 filed in Taiwan, Republicof China on Feb. 13, 2015, and China Patent Application No(s).201610023838.1 filed in People's Republic of China on Jan. 14, 2014 theentire contents of which are hereby incorporated by reference.

BACKGROUND

1. Technical Field

The invention relates to a joint prosthesis, in particular to a kneejoint prosthesis.

2. Related Art

Knee is the biggest human joint. It sustains a person's weight and letsthe leg finely exercise flexion and extension. It includes the femoralcondyles of the femur distal end, the tibial plateau of the tibiaproximal end, the ligament (for example, the anterior cruciate ligament,the posterior cruciate ligament, the medial ligament and the lateralligament, etc.), and the joint cartilage and meniscus. However,development defects of lower limb joints, bad standing, excessiveexercises or ageing usually cause wears of joint cartilage and meniscus,so the lubricating fluid of knee articular capsule becomes lessresulting in knee pain, swelling, difficult squat or other exerciseimpediment for example degenerative knee joint disease. More serious, itcauses bowleg and the patient walks difficultly.

Total keen joint replacement is the most effective treatment for thesymptom, it effectively alleviates pain due to arthritis and deformedjoint and improves exercise range of the joint after implanting the kneejoint prosthesis. But it still has some disadvantages.

A conventional knee joint prosthesis for total keen joint replacement isshown in FIG. 9A and FIG. 9B. The knee joint prosthesis includes afemoral implant a and a tibia assembly b. The tibia assembly b includesa tibial plate b1, a joint liner b2 and a tibial implant portion b3. Thefemoral implant a is nailed into the femoral condyles of the femur Fe bya femoral nail a2, and the tibia assembly b is fixed to the tibialplateau in the human body by the tibial implant portion b3 implantedinto the tibia T. The central protrusion b22 of the joint liner b2 andthe indentation a3 of the femoral implant a are disposed and limitedcorrespondingly, so that the abutting surface a1 of the femoral implanta which faces the tibia T abuts the carry surface b21 of the joint linerb2 to rotate relatively, and the lower limb of the patient can exerciseflexion and extension.

However, due to the life time of the knee joint prosthesis, the jointliner b2 substituting the knee meniscus suffers from the friction causeby the abutting surface a1 of the femoral implant a, thus it is damagedand incapable to use. Such the conventional knee joint prosthesis shouldbe replaced over 15-20 years.

Besides, when the patient's knee exercises at an excessively angle orvery intensively, the central protrusion b22 on the joint liner b2 maywear overly or may depart from the indentation a3 of the femoral implanta which causes dislocation. Even the central protrusion b22 on the jointliner b2 is severed by side intensive strike or rotation of the femoralimplant a. In such situation, the knee joint prosthesis should bereplaced.

In the above situation that the knee joint prosthesis should bereplaced, because the original tibial implant portion b3 or the originalfemoral nail a2 has respectively damaged the tibia proximal end or thefemur distal end overly, when implanting a new femoral implant a ortibia assembly b, it is necessary to thwack an additional long bone pegon the longitudinal direction of the femur Fe or the tibia T so thefemoral implant a or the tibia assembly b are not loosen and stablydisposed in the femur Fe or the tibia T. However, such thwacking anadditional long bone peg will cause extra damage on the patient's bone.Even it is necessary to thwack a longer bone peg to keep the femoralimplant a stable in the femur Fe or the tibia assembly b stable in thetibia T when implanting new femoral implant a or the tibia assembly b,so it causes more serious damage. Therefore, it is an unsolved problemin the field to dispose the joint prosthesis component stably on theimplanted portion without using bone peg.

Besides, when the femoral condyles or the tibial plateau arerespectively implanted into the femoral implant a or the tibia assemblyb, the orthopedic surgeons generally applies a layer of bone cement (orbiological glue) to the contact surface of the femoral implant a and thefemoral condyles or the contact surface of the tibia assembly b and thetibial plateau to increase the stability of the femoral implant a or thetibia assembly b. However, before solidified, the bone cement easilyenters systemic circulation from the artery of the injured area due tosurgery. It may cause the skin or muscle tissue at the affected areanecrosis, more seriously, it may cause the patient death due tomyocardial infarction. Therefore, it is also an unsolved problem to keepconsiderable stability of the implanted knee joint prosthesis whendecreasing the usage of the bond cement.

Furthermore, when utilizing the conventional knee joint prosthesis asshown in FIG. 9A and FIG. 9B to perform total keen joint replacement, itis necessary to resect the anterior cruciate ligament and the posteriorcruciate ligament of the patient. Accordingly, the relative actionbetween the femoral implant a and the tibia assembly b only relies onthe indentation a3 of the femoral implant a and the fit of the centralprotrusion b22 correspondingly disposed on the joint liner b2. Thus, thestability of the patient's postoperative knee is insufficient, and thepatient's postoperative knee cannot bend at too large angle. Therefore,it is also an unsolved problem to provide a knee joint prosthesisadapted to cruciate ligament-retaining when performing total keen jointreplacement so as to retain the anterior cruciate ligament and theposterior cruciate ligament of the patient.

SUMMARY

A knee joint prosthesis includes a tibial component and a femoralcomponent. The tibial component has a top surface, a bottom surfaceopposite to the top surface and a first slot passing through the topsurface and the bottom surface for accommodating a cruciate ligament.The tibial component has at least one first protrusion disposed on thebottom surface, and the first protrusion has a plurality of firstthrough holes. The femoral component is carried by the tibial componentand has a second slot for accommodating the cruciate ligament. Thefemoral component has at least one second protrusion disposed on asurface thereof against the tibial component, and the second protrusionhas a plurality of second through holes.

In one embodiment, the tibial component includes at least one sidewalland an engagement groove, and the sidewall surrounds the first slot andthe engagement groove is disposed on the sidewall.

In one embodiment, the first protrusion has a first cutting edge and afirst base, the first base is disposed between the first cutting edgeand the bottom surface of the tibial component, and the first cuttingedge gradually becomes thinner along the extending direction thereof.

In one embodiment, the tibial component has a through hole which doesnot overlap with the first base.

In one embodiment, the tibial component has a first side wall having aplurality of first apertures.

In one embodiment, the femoral component has two holding notchesrespectively located at two sides thereof.

In one embodiment, the second protrusion has a second cutting edge and asecond base, the second base is disposed between the second cutting edgeand the surface of the femoral component away from the tibial component,and the second cutting edge gradually becomes thinner along theextending direction thereof.

In one embodiment, the second protrusion has at least one positionpillar, and the position pillar is disposed on the middle segment of thesecond protrusion.

In one embodiment, the knee joint prosthesis further comprises at leastone pad. The pad is located between the tibial component and the femoralcomponent.

In one embodiment, the pad has a second side wall, the second side wallhas a plurality of second apertures.

In one embodiment, the pad has an abrasion meter.

A tibial component comprises a top surface, a bottom surface oppositethe top surface and a first slot passing through the top surface and thebottom surface for accommodating a cruciate ligament. The tibialcomponent has at least one protrusion disposed on the bottom surface andthe protrusions has a plurality of through holes.

In one embodiment, the tibial component has at least one sidewall and anengagement groove, and the sidewall surrounds the slot and theengagement groove is disposed on the sidewall.

In one embodiment, the first protrusion has a first cutting edge and afirst base, the first base is disposed between the first cutting edgeand the bottom surface of the tibial component, the first cutting edgegradually becomes thinner along the extending direction thereof.

In one embodiment, the tibial component has a through hole which doesnot overlap with the first base.

In one embodiment, the tibial component has a first side wall, the firstside wall has a plurality of first apertures.

A femoral component is disposed corresponding to a tibial component.

The tibial component carries the femoral component. The femoralcomponent includes a slot for accommodating a cruciate ligament. Thefemoral component has at least one protrusion on a surface thereofagainst the tibial component, and the protrusion has a plurality ofthrough holes.

In one embodiment, the femoral component comprises two holding notchesrespectively located at two sides thereof.

In one embodiment, the protrusion has a cutting edge and a base, thebase is disposed between the cutting edge and the surface of the femoralcomponent away from the tibial component, and the cutting edge graduallybecomes thinner along the extending direction thereof.

In one embodiment, the protrusion has at least one position pillar, theposition pillar is disposed on the middle segment of the protrusion.

As mentioned above, as to the knee joint prosthesis, the tibialcomponent and the femoral component thereof, because the tibialcomponent and the femoral component respectively have at least one firstprotrusion and at least one second protrusion, and each of the firstprotrusion and the second protrusion respectively has at least one firstthrough hole and at least one second through hole. After the tibialcomponent and the femoral component are respectively implanted into thetibial plateau and the femoral condyles, the first protrusion isinserted into the tibial plateau and the second protrusion is insertedinto the femoral condyles. The bone trabeculae in postoperative healingprocess will grow to pass through the first through hole and the secondthrough hole so as to fix the tibial component and the femoral componentto the implanted portion. Moreover, if the knee joint prosthesis isneeded to replace in the future, the bone trabeculae can grow in thefirst through hole and the second through hole to fix the replacedtibial component or femoral component.

In addition to the above effect of the knee joint prosthesis and thetibial component and the femoral component thereof, in one embodiment,because the tibial component and the femoral component respectively havethe first slot and the second slot disposed corresponding to each otherfor accommodating the cruciate ligament of the patient's knee, theorthopedic surgeons can adopt cruciate ligament-retaining to keep thestability of the postoperative joint and reduce the wear of the newjoint when performs total keen joint replacement.

BRIEF DESCRIPTION OF THE DRAWINGS

The embodiments will become more fully understood from the detaileddescription and accompanying drawings, which are given for illustrationonly, and thus are not limitative of the present invention, and wherein:

FIG. 1 is a schematic diagram showing the assembly of the knee jointprosthesis according to an embodiment;

FIG. 2 is a schematic diagram showing the femoral component of the kneejoint prosthesis in FIG. 1;

FIG. 3 is a schematic diagram showing the tibial component and the padof the knee joint prosthesis in FIG. 1;

FIG. 4A is a schematic diagram showing the knee joint prosthesis in FIG.1 is implanted into the patient's knee and observed in theanterior-posterior direction.

FIG. 4B is a schematic diagram showing the knee joint prosthesis in FIG.1 is implanted into the patient's knee and observed in themedial-lateral direction.

FIG. 4C is a schematic diagram showing the direction for implanting thetibial component and the femoral component of the knee joint prosthesisin FIG. 1 into the patient's knee.

FIG. 5A to FIG. 5G are schematic diagrams showing the tibial componentof the knee joint prosthesis in FIG. 1;

FIG. 6A to FIG. 6C are schematic diagrams showing the tibial componentand the pad of the knee joint prosthesis in FIG. 1;

FIG. 7A to FIG. 7B are schematic diagrams showing the assembly of theknee joint prosthesis according to another embodiment;

FIG. 8A is a schematic diagram showing the tibial component of the kneejoint prosthesis in FIG. 1 and auxiliary implantation device;

FIG. 8B to FIG. 8D are schematic diagrams showing the first protrusionin the tibial component of the knee joint prosthesis in FIG. 2;

FIG. 8E is a schematic diagram showing another femoral component of theknee joint prosthesis according to another embodiment; and

FIG. 9A to FIG. 9B are schematic diagrams showing the conventional kneejoint prosthesis.

DETAILED DESCRIPTION OF THE INVENTION

The embodiments of the invention will be apparent from the followingdetailed description, which proceeds with reference to the accompanyingdrawings, wherein the same references relate to the same elements.Moreover, the terms proximal, distal, anterior, posterior, medial, orlateral, etc. in the following embodiments are defined according toanatomy posture and indicative direction. Namely, “proximal” refers tofacing the head, “distal” refers to facing the foot; “anterior” refersto facing the ventral of the body, “posterior” refers to facing to thedorsal of the body; “medial” refers to facing the central line of thebody, “lateral” refers to departing from the central line of the body.Although the following embodiments take human knee for example, they arenot limited thereto. Namely, the knee joint prosthesis of the followingembodiments could be applied to other animal knee which has the same orsimilar anatomical structure.

First, referring to FIG. 1, FIG. 4A and FIG. 4B, FIG. 1 is a schematicdiagram showing the assembly of the knee joint prosthesis according toan embodiment, FIG. 4A and FIG. 4B are schematic diagrams showing theknee joint prosthesis in FIG. 1 is implanted into the patient's knee. InFIG. 4A, the observed direction is the anterior-posterior direction ofthe patient's knee, and in FIG. 4B, the observed direction is themedial-lateral direction of the patient's knee. The relative positionsof the femur Fe, the tibia T, the fibula Fi and the patella P shown inthe figures are diagrammatic. The person skilled in the art shouldunderstand the relative positions and disposal relationship of the femurFe, the tibia T, the fibula Fi and the patella P after implanting theknee joint prosthesis K in the embodiment according to the figures andthe description. The knee joint prosthesis K includes a tibial component1 and a femoral component 2. The tibial component 1 includes a topsurface 11 and a bottom surface 12 opposite to the top surface 11. Thetibial component 1 has at least one first protrusion 13 disposed on thebottom surface 12. In the embodiment, a plurality of the firstprotrusions 13 are disposed for example. Each of the first protrusions13 has at least one first through hole 14. In the embodiment, aplurality of the first through holes 14 are disposed for example. Thefemoral component 2 is disposed corresponding to the tibial component 1,and the top surface 11 of the tibial component 1 carries the femoralcomponent 2. In the embodiment, “carry” means two manners: a surface 22the femoral component 2 facing the tibial component 1 directly abuts thetop surface 11 of the tibial component 1; or alternatively, anadditional component (descripted later) is utilized to buffer, so thefemoral component 2 is supported on the top surface 11 of the tibialcomponent 1 and the surface 22 of the femoral component 2 facing thetibial component 1 does not directly contact the top surface 11 of thetibial component 1 in an indirect carrying manner. In details, thefemoral component 2 is slidably positioned at the tibial component 1. Asshown in the figure, the top surface 11 of the tibial component 1 facesthe surface of the femoral component 2 for engaging with the pad 3.After implanted, the bottom surface 12 of the tibial component 1substantially contacts the surface of the tibia proximal end. Thematerial of the tibial component 1 can be biocompatible metal material,for example but not limited to titanium, titanium alloy, Co—Cr—Mo alloy(cobalt-chromium-molybdenum alloy) or 316 stainless steel.

Referring to FIG. 1 to FIG. 3, FIG. 2 is a schematic diagram showing thefemoral component of the knee joint prosthesis in FIG. 1, and FIG. 3 isa schematic diagram showing the tibial component and the pad of the kneejoint prosthesis in FIG. 1. The femoral component 2 roughly looks likean arc and includes a second slot 25 which divides the femoral component2 into a lateral condyle portion 2 a and a medial condyle portion 2 bconnected by a connection portion 2 c. Moreover, the connection portion2 c can also act as the sliding surface of the patella P as shown inFIG. 4B. FIG. 3 is a schematic diagram showing the tibial component andthe pad of the knee joint prosthesis in FIG. 1. Besides, the tibialcomponent 1 also includes a first slot 15 which passes through the topsurface 11 and the bottom surface 12 and divides the tibial component 1into a first portion (lateral side) 1 a and a second portion (medialside) 1 b. The first portion 1 a and the second portion 1 b areconnected by the connection portion 1 c. The lateral condyle portion 2 aof the femoral component 2 is correspondingly and slidably disposed onthe first portion (lateral side) 1 a of the tibial component 1;similarly, the medial condyle portion 2 b of the femoral component 2 iscorrespondingly and slidably disposed on the second portion (lateralside) 1 b of the tibial component 1.

To easily hold the femoral component 2 for the surgeon in a surgicaloperation to aim and to press for implantation, at least one holdingnotch 26 is disposed at each of the two opposite sides of the femoralcomponent 2 with respect to the second slot 25 for clamping andpressing. In other words, the second slot 25 is disposed between the twoholding notches 26. The holding notch 26 may be a rectangle notch, awedge notch or a ball notch, but it is not limited thereto. It isrequired to match the clamping apparatus for operation. The quantity ofholding notch 26 is not limited, too.

Moreover, the depth of the first slot 15 in the sagittal axial ispreferably 30% to 90% of the length of the tibial component 1 in thesagittal axial, more preferably 50% to 80%, so as to accommodate theanterior cruciate ligament ACL and the posterior cruciate ligament PCLby the first slot 15 (as shown in FIG. 4A. The projection length of thedepth of the second slot 25 on the traverse plane of the patient's kneealong the sagittal axial is preferable 30% to 90% of that of the femoralcomponent 2 on the traverse plane of the patient's knee along thesagittal axial, more preferably 50% to 80%, so as to benefit the secondslot 25 to accommodate the anterior cruciate ligament ACL and theposterior cruciate ligament PCL. The measurement of the depth and lengthmention above is based on that the tibial component 1 and the femoralcomponent 2 are implanted into the patient's knee and buckling angle iszero (equivalently the patient stands or the lower limbs get straight).The person skilled in the art should understand that the ratio of thedepth of the first slot 15 to the length of the tibial component 1 onthe sagittal axial and the ratio of the depth of the second slot 25 tothe projection length of the femoral component 2 on the traverse planeof the patient's knee along the sagittal axial are not necessarilyequal. The first slot 15 and the second slot 25 are required toaccommodate the anterior cruciate ligament ACL and the posteriorcruciate ligament PCL, and they can be adjusted depending on actualsituation.

Referring to FIG. 1, FIG. 4A and FIG. 4B, after the tibial component 1is implanted into the tibial plateau of the patient, the firstprotrusions 13 are inserted into the tibial plateau. The tibial plateaumeans the portion of the tibia T which looks like a platform at thetibia proximal end. In the postoperative healing process, the bonetrabeculae will grow to pass through the first through holes 14 on thefirst protrusions 13 so as to fix the tibial component 1 to the tibialplateau. Moreover, if it needs replacement in the future due tocomponent wear, after implanting the new tibial component 1, the bonetrabeculae will grow in the first through hole 14 to fix the replacedtibial component 1. Moreover, the more quantity of the first throughholes 14 on the first protrusions 13, the better performance of fixingthe tibial component 1 resulting from that the bone trabeculae grows topass through the first through holes 14 to grasp the first protrusions13. The thickness of the first protrusion 13 is preferably between 0.1cm to 0.7 cm, more preferably between 0.3 cm and 0.4 cm. The thicknessof the first protrusion 13 means the thickness of the connection portionof the first protrusion 13 connecting to the bottom surface 12.Moreover, in a preferable example, each of the first protrusions 13 hasa plurality of the first through holes 14. The first through holes 14 onthe first protrusion 13 are distributed from sparse to dense along thedirection from close to the tibial component 1 to departing from thetibial component 1. The hole diameter of the first through hole 14 ispreferably between 1 mm and 2 mm, and the interval between the firstthrough holes 14 are preferably between 3 mm to 5 mm. Moreover, in oneembodiment, the surface of each first protrusion 13 may be processed toform a rough surface by for example abrasive blasting or chemicaletching. As a result, in the postoperative healing process, the bonetrabeculae will grow on the surface of the first protrusion 13.

Referring to FIG. 8, to abate the risk of crash of the first protrusion13 in implantation process, the first protrusion 13 may further have afirst base 132 and a first cutting edge 131. The first base 132 may berectangle (like (a) in FIG. 8B), square (like (b) in FIG. 8B), stripshape, trapezoid (like (c) and (d) in FIG. 8B), wedge, etc., but it isnot limited thereto. It is required to have a wider contact base wherethe first cutting edge 131 can be stably disposed. The first cuttingedge 131 extends opposite the tibial component 1 (namely, from thebottom surface 12 to the distal tibial). Meanwhile, the first cuttingedge 131 gradually becomes thinner along the extending directionthereof.

The femoral component 2 has at least one second protrusion 23 disposedon the surface 21 against the tibial component 1. In the embodiment, aplurality of the second protrusions 23 are disposed for example. Each ofthe second protrusions 23 has at least one second through hole 24. Inthe embodiment, a plurality of the second through holes 24 are disposedfor example. As shown in FIG. 2, the surface 21 of the femoral component2 against the tibial component 1 is the inner surface of the femoralcomponent 2 looking like an arc structure, and substantially contactsthe femur distal end after implanted. The material of the femoralcomponent 2 can similarly be biocompatible metal material, for examplebut not limited to titanium, titanium alloy, Co—Cr—Mo alloy or 316stainless steel. Similarly to the first protrusion 13, to abate the riskof crash of the second protrusion 23 in implantation process, the secondprotrusion 23 may have a the second base and a second cutting edge (notshown in the figure). The configuration of the second base is the sameor similar with the first base 132. It is required to have a widercontact base where the second cutting edge can be stably disposed. Thesecond cutting edge extends against the arc inner surface 21 of thetibial component 1 (namely, from the surface 21 to proximal femoral).Meanwhile, the second cutting edge gradually becomes thinner along theextending direction thereof.

Similar to the tibial component 1, as to the femoral component 2implanted into the femoral condyles of the femur Fe, the secondprotrusion 23 will be inserted into the corresponding femoral condyles.In the postoperative healing process, the bone trabeculae will grow topass through the second through hole 24 on the second protrusion 23 soas to fix the femoral component 2 to the femoral condyles. Moreover, ifit needs replacement in the future due to component wear, afterimplanting the new femoral component 2, the bone trabeculae will grow inthe second through hole 24 to fix the replaced femoral component 2. Thepreferable thickness of the second protrusion 23 is between 0.1 cm to0.7 cm, more preferably between 0.3 cm and 0.4 cm. Here, the thicknessof the second protrusion 23 means the thickness of the second protrusion23 connecting to the surface 21. Moreover, in a preferable example, eachof the second protrusions 23 has a plurality of the second through holes24. The second through holes 24 on the second protrusion 23 aredistributed from sparse to dense along the direction from close to thefemoral component 2 to departing from the femoral component 2. The holediameter of the second through hole 24 is preferably between 1 mm to 2mm, and the interval between the second through holes 24 is preferablybetween 3 mm to 5 mm. Moreover, in one embodiment, the surface of eachsecond protrusion 23 may be processed to form a rough surface by forexample abrasive blasting or chemical etching. As a result, in thepostoperative healing process, the bone trabeculae will grow on thesurface of the second protrusion 23.

Besides, although the first protrusion 13 and the second protrusion 23in the embodiment are integrated as a whole one element on the bottomsurface 12 of the tibial component 1 and the arc inner surface 21 of thefemoral component 2 against the tibial component 1 for example, they arenot limited thereto. Namely, in other embodiments, the first protrusion13 and the second protrusion 23 can be detachable, during usage, it isassembled with the bottom surface 12 of the tibial component 1 and thearc inner surface 21 of the femoral component 2 against the tibialcomponent 1.

Referring to FIG. 4A and FIG. 4B, after implanting the tibial component1 into the tibial plateau of the patient, the anterior cruciate ligamentACL and the posterior cruciate ligament PCL of the patient's knee areaccommodated in the first slot 15. Similarly, after implanting thefemoral component 2 into the femur distal end of the patient, theanterior cruciate ligament ACL and the posterior cruciate ligament PCLof the patient's knee are accommodated in the second slot 25. Thus,after the orthopedic surgeon performs keen joint replacement to implantthe knee joint prosthesis K into the patient's knee, one can adoptcruciate ligament-retaining namely retain the anterior cruciate ligamentACL and the posterior cruciate ligament PCL of the patient instead ofresection during implanting to keep the stability of the patient'spostoperative joint and reduce the wear of the new joint. Moreover, thepostoperative knee can keep considerable exercise freedom (for examplebuckling, stretching, outward rotation, inward rotation, eversion andinversion, etc.)

For easily implanting the tibial component 1, in the embodiment, thefirst protrusion 13 extends along a direction against the tibialcomponent 1 (namely extends from the bottom surface 12 toward the tibiadistal end). Concurrently, the first protrusion 13 gradually becomesthinner along the extending direction of the first protrusion 13 and itis like a fin or a blade. The method of implanting the tibial component1 includes but is not limited to nailing (directly making the tibialcomponent 1 abut the tibia proximal end and applying a forcesubstantially parallel to the tibia the longitudinal direction, andthwacking the tibial component 1 into the tibial plateau), slide-in(sliding along the direction of anterior-to-posterior of the knee andinserting obliquely downwardly), adhesion (applying bone cement orbiological glue to the bottom surface 12 so that the tibial component 1is adhered to the tibial plateau), or any combination of the previousmethods. To smooth the implantation of the tibial component 1, anadditional auxiliary implantation device can be used. Referring to FIG.8A, auxiliary implantation device 4 comprises a position block 41, afixing screw 42, and a wrench 43. The position block 41 is approximatelya cylinder, a plurality of position grooves 411 (may be parallel groovesor screw thread) are disposed on each of two opposite outer sidesurfaces thereof or disposed around the outer side surface thereof, andit has a fixing screw hole 412 where fixing screw 42 is screwed. Thefixing screw hole 412 extends inwardly along its major axis from one endof the position block 41. The first portion 1 a, the connection portion1 c and the second portion 1 b of the tibial component 1 comprise atleast one sidewall which surrounds the first slot 15, and the engagementgrooves (maybe parallel grooves or screw thread) 19 (as shown in FIG. 3)are disposed on the sidewall. By using the position grooves 411 on theouter side surface of the position block 41 and the engagement grooves19 on the sidewall, the position block 41 can be screwed or embeddedwith the tibial component 1. One end of the wrench 43 is a lock end 431,the other end opposite to the lock end 431 is a handle end 433. The lockend 431 further has a lock hole 432. In other embodiments, the lock end431 may not have the lock hole 432. The wrench 43 further has anabutting wall 434 disposed between the lock end 431 and the handle end433, preferably near the lock end 431. The position block 41 furthercomprises an opening 413 where the lock end 431 of the wrench 43 isinserted. The opening 413 extends from the outer side surface of theposition block 41 inwardly along the direction approximatelyperpendicular to the major axis of the position block 41.

When the lock end 431 of the wrench 43 is inserted into the opening 413of the position block 41, the lock hole 432 is aligned to the fixingscrew hole 412 and then the fixing screw 42 can be inserted into thefixing screw hole 412 and the lock hole 432 to secure the position block41 to the wrench 43. In other embodiments, because the lock end 431 doesnot have the lock hole 432, when the lock end 431 of the wrench 43 isinserted into the opening 413 of the position block 41, the fixing screw42 can be inserted into the fixing screw hole 412 to secure the positionblock 41 to the wrench 43. Therefore, it is possible to omit to alignthe lock hole 432 to the fixing screw hole 412. Meanwhile, the abuttingwall 434 abuts the connection portion 1 c of the tibial component 1.Thus, it seems that the abutting wall 434 of the wrench 43 and theposition block 41 clamp the connection portion 1 c. Therefore, inimplanting the tibial component 1, by using the rear portion of thefirst protrusion 13 of the tibial component 1 to abut the patient'stibial plateau, the surgeon can take the place of the patient's tibialplateau abutted by the first protrusion 13 as the fulcrum and hold thehandle end 433 of the wrench 43, and then slides the first protrusion 13of the tibial component 1 into the patient's tibial plateau. Further,gradienters 435, 436 can be disposed on the wrench 43 so the surgeon canobserve that the first portion 1 a and the second portion 1 b of thetibial component 1 both are horizontal to the same level afterimplanting the tibial component 1.

Referring to FIG. 8C, the first protrusion 13 may be thinner and extendlonger at its rear portion so the rear portion is sharper and the frontportion is blunter (like cleaver). In the implanting process, the rearportion of the first protrusion 13 of the tibial component 1 contact andabut the patient's tibial plateau first. As a result, in implanting thetibial component 1 in the patient's tibia condyle by sliding, thesharper rear portion of the first protrusion 13 firstly breaks the bonetissue of the patient's tibia condyle, and then the middle segment andthe front portion of the first protrusion 13 can accordingly smoothlycut into the bone tissue of the patient's tibia condyle to complete theimplantation of the tibial component 1. Moreover, because afterimplantation, the posterior of the tibial component 1 carries heavierweight than the anterior does. The extension of the rear portion of thefirst protrusion 13 is longer than the extension of the front portion ofthe first protrusion 13 so as to stably support the tibial component 1.It is noted that although the first through holes are omitted in FIG.8C, actually the first protrusion 13 comprises a plurality of the firstthrough holes 14. Referring to FIG. 8D and FIG. 4C, a receded incision134 may be disposed on the rear portion of the first protrusion 13 topreferably conform the tibia T. Moreover, when implanting the tibialcomponent 1 in the patient's tibia condyle by sliding, the recededincision 134 on the first protrusion 13 abutting the patient's tibialplateau can act as the point applied with force, and it is also a guidefor the surgeon to press downwardly. The receded incision 134 let thefirst protrusion 13 completely covered by bone tissue in theimplantation process and reserve some gaps, too. Therefore, it preventsthe first protrusion 13 from being stuck when cutting into the tibialplateau. It is easier for the first protrusion 13 to slide into thepatient's tibial plateau. It is noted that although the first throughholes 14 are omitted in FIG. 8D, actually the first protrusion 13comprises a plurality of the first through holes 14. Moreover, theextension of the first protrusion 13 may be alternatively various inlength along it major axis, such as a mountain having summits andvalleys arranged alternatively along its ridgeline, so the firstprotrusions 13 cut into the tibial plateau in various depth.

Similarly, for easily implanting the femoral component 2, in theembodiment, the second protrusion 23 extends a direction against thefemoral component 2 (namely extends from the surface 21 toward theproximal end direction of the femur). Concurrently, the secondprotrusion 23 gradually becomes thinner along the extending direction ofthe second protrusion 23 and it is like a fin or a blade. The method ofimplanting the femoral component 2 preferably is nailing or pushing(directly making the femoral component 2 abut the femur distal end andapplying a force substantially parallel to the femur the longitudinaldirection, and thwacking the femoral component 2 into the femoralcondyles). Moreover, the extension of the second protrusions 23 may bealternatively various in length along it major axis, such as a mountainhaving summits and valleys arranged alternatively along its ridgeline,so the second protrusions 23 are thwacked into the femoral condyles invarious depth.

Moreover, referring to FIG. 8E, to prevent the implanted femoralcomponent 2 from moving on sagittal plane, the second protrusion 23 mayfurther comprise a position pillar 231 disposed on the middle segment,or on a location near the middle segment, of the second protrusion 23which is like fin or knife. Thus, before implanting, position holesshould be drilled in the corresponding femoral condyle. As a result,after implanting the femoral component 2 in the corresponding femoralcondyle, the second protrusion 23 is inserted into the correspondingfemoral condyle as mentioned previously, and the position pillar 231 isinserted into the position hole drilled in the femoral condyle. Thus,the femoral component 2 can be stably disposed, and it slide or rotateover the sagittal plane as little as possible. In addition to nailing orpushing mentioned previously, the femoral component 2 can be implantedinto the patient's femoral condyle by slide-in (sliding along thedirection of anterior-to-posterior of the knee and inserting obliquelyupwardly), adhesion (applying bone cement or biological glue to thesurface 21 against the tibial component 1 so that the femoral component2 is adhered to the femoral condyles) or any combination of the previousmethods. However, if implanting by sliding, preferably the positionpillar 231 is omitted on the second protrusion 23.

Referring to FIG. 4C, it is a schematic diagram showing the directionfor implanting the tibial component and the femoral component of theknee joint prosthesis in FIG. 1 into the patient's knee. When theorthopedic surgeons performs keen joint replacement, preferably, theouter cartilage of condyle of femoral Fe is processed first to lightenthe damage to the patient's bone. For easily implanting the tibialcomponent 1 or the femoral component 2 by slide-in, the extendingdirection of the first protrusion 13 or the second protrusion 23 issubstantially parallel to the sagittal plane of the patient's knee.However, it is not limited thereto.

Referring to FIG. 5A to FIG. 5C, they are schematic diagrams showing thetibial component of the knee joint prosthesis in FIG. 1. Similarly, foreasily implanting the tibial component 1 by slide-in, each of the firstprotrusions 13 of the tibial component 1 has a first longitudinaldirection L1, which is parallel to its major axis, and each of the firstlongitudinal directions L1 is substantially parallel to each other.Besides, the fin structure or the blade structure of each of the firstprotrusions 13 in FIG. 5A extends from the front to the rear of tibialcomponent 1 and looks like a complete arc structure. As shown in FIG.5B, the fin structure or the blade structure of each of the firstprotrusions 13 extends only from the center to the rear and looks like ahalt arc structure. Referring to FIG. 5C, for increasing the structurestrength of the connection portion 1 c and reducing the break of theconnection portion 1 c caused by stress due to low structure strengthwhen implanted, at least one additional first protrusion 13 c can bedisposed on the bottom surface 12 of the connection portion 1 c.Additional two are disposed in the figure for example.

Besides, referring to FIG. 5D to FIG. 5G, they are schematic diagramsshowing other examples of the tibial component 1 of the knee jointprosthesis in FIG. 1. When implanting by the method other than slide-in,the longitudinal direction of the first protrusion 13 can also be thedirection along the coronal plane of the knee or other directions.Namely, as shown in FIG. 5D, the first protrusion 13 is disposed alongthe front-rear direction of the tibial component 1 and substantiallyparallel to the sagittal plane of the patient's knee, but alternativelyas shown in FIG. 5E, the first protrusion 13 is roughly disposed alongthe front-rear direction of the tibial component 1 but not substantiallyparallel to the sagittal plane of the patient's knee. Or alternativelyas shown in FIG. 5F, the first protrusion 13 is disposed along themedial-lateral direction of the tibial component 1 and substantiallyparallel to the coronal plane direction of the knee. Moreover, as shownin FIG. 5G, combining the above directions, the first protrusions 13interlace on the bottom surface 12 of the tibial component 1.

Similar to the previous design of the first protrusion 13 in apreferable example for easily implanting by slide-in as shown in FIG. 2,each of the second protrusions 23 of the femoral component 2 has asecond longitudinal direction L2, which is parallel to its major axis,and each of the second longitudinal directions L2 is substantiallyparallel to each other. However, they are not limited thereto. Namely,each of the second protrusion 23 can extend from the front to the rearof the femoral component 2 and look like a complete arc structure, oralternatively extend only from the center to the rear of the femoralcomponent 2 and look like a half arc structure. Alternatively, thesecond protrusion 23 can be disposed along the sagittal plane, thecoronal plane direction or other direction or combination of theprevious directions of the knee.

Besides, in the embodiment, the knee joint prosthesis K further includesat least one pad 3. Referring to FIG. 1 and FIG. 3, the knee jointprosthesis K includes two pads 3 for example. The pads 3 are locatedbetween the tibial component 1 and the femoral component 2, and can berespectively engaged with the top surface 11 of first portion 1 a andthe top surface 11 of the second portion 1 b. The top surface 11 of thefirst portion 1 a or the top surface of the second portion 1 b lookslike a shallow-dish concave, and the surfaces of the two pads 3 whichcontact them are respectively designed with a convex corresponding tothe shallow-dish concave. The pad 3 can have a circular pit. The surfacefacing the femoral component 2 can be designed to carry the lateralcondyle portion 2 a or the medial condyle portion 2 b of the femoralcomponent 2 and have an arc concave surface on which they can slide.Thus, the pads 3 act as the knee meniscus. In one embodiment, if thesurface of the pad 3 facing the femoral component 2 is a curved concave,the thickness at the curved concave/the thickness at the periphery ofthe pad 3 may be 2 mm/6 mm, 3 mm/8 mm, 4 mm/10 mm, or 5 mm/12 mm. Afterimplanted into the patient's knee, the femoral component 2 abuts the pad3 and the femoral component 2 can slide or rotate with respect to thetibial component 1. Referring to FIG. 3, although the pad 3 in theembodiment for example but not limited to has a slidable curved concaveand looks like a disk. The preference is that the pad 3 has a concavesurface to carry the lateral condyle portion 2 a or the medial condyleportion 2 b of the femoral component 2 on which they can slide. Namely,the pad 3 having circular pit is also preferable. In the embodiment, thematerial of the pad 3 can be biocompatible plastic including but notlimited to medical grade PVC, Polyethylene, PEEK, Polycarbonate, PEIresin (Ultem®, Polyetherimide resin), Polysulfone, Polypropylene orPolyurethane. Further, the pad 3 has a first engagement portion 31, thefirst engagement portion 31 fits the second engagement portion 16 of thetibial component 1, and the second engagement portion 16 of the tibialcomponent 1 is adjacent to the first slot 15. As shown in FIG. 3, thesecond engagement portions 16 on the tibial component 1 in theembodiment are disposed on the first portion 1 a and the second portion1 b close to the first slot 15. In a preferable example, when the pad 3is disposed on the tibial component 1, they are connected to each otheronly by the first engagement portion 31 of the pad 3 and the secondengagement portion 16 of the tibial component 1 at medial side.Moreover, the first engagement portion 31 of the pad 3 is a rodconformation and the second engagement portion 16 of the tibialcomponent 1 is a circular through hole, so that the first engagementportion 31 of the pad 3 and the second engagement portion 16 of thetibial component 1 constitutes a pivot structure. The lateral of the pad3 and the tibial component 1 are not fixed so the femoral component 2 ofthe implanted knee joint prosthesis K can still rotate in outwardrotation and inward rotation with respect to the tibial component 1 tokeep freedom of outward rotation and inward rotation of the patient'spostoperative knee. However, the conformations of the first engagementportion 31 of the pad 3 and the second engagement portion 16 of thetibial component 1 are not limited. The first engagement portion 31 ofthe pad 3 can be the rod conformation mentioned above, or the firstengagement portion 31 a can be a bolt conformation in FIG. 6B or thebump in FIG. 6C for example but not limited to hemispherical bump orhalf-moon bump. In a preferable example in the embodiment, the fitbetween the first engagement portion 31 of the pad 3 and the secondengagement portion 16 of the tibial component 1 is concave-convex. Thatwhich one is concave or which one is convex is not limited.

As shown in FIG. 3, the tibial component 1 further has at least onethrough hole 18 on the first portion (lateral) 1 a and the secondportion (medial) 1 b. In the embodiment, there are a plurality of thethrough holes for example, but the quantity is not limited. The throughhole 18 passes through the top surface 11 and the bottom surface 12 andpreferably keeps away the location where the first protrusion 13 isdisposed. Such design lets the tibial component 1 be lightweight andexhausts particles caused by the friction between the pad 3 and thetibial component 1. The diameter of the through hole 18 is preferablysmaller than or equal to the distance between the two adjacent the firstprotrusions 13.

Moreover, a first side wall 33 may be disposed on the outer sidewall ofthe pad 3. The first side wall 33 has at least one first aperture. Inthe embodiment, there are for example but not limited to a plurality ofthe first apertures. In the postoperative healing process, the firstapertures are tightly clutched by the tissue at the patient's implantedportion so the pad 3 and the patient's knee can act together and thepostoperative stability becomes better. The dimension of the firstaperture is the same or similar with the first through hole or thesecond through hole on the first protrusion 13 or the second protrusion23. The height of the first side wall 33 is preferably equal to ⅔ of thethickness of the pad 3, but it is not limited thereto. The material ofthe first side wall 33 is biocompatible metal material including forexample but not limited to titanium, titanium alloy, Co—Cr—Mo alloy or316 stainless steel. The installation manner can be like sticking shownin FIG. 3 (a gap is kept between the first side wall 33 and the outersidewall of the pad 3) or completely attaching to the outer sidewall ofthe pad 3 shown in FIG. 6A, or inserting two ends of the first side wall33 into the position holes (or position notches) on the outer sidewallof the pad 3, but it is not limited thereto. The first side wall 33 maycompletely or incompletely circle the outer sidewall of the pad 3, too.Similarly, for the implanted tibial component 1 to be tightly clutchedby the tissue at the patient's implanted portion and act with thepatient's knee for better postoperative stability, as shown in FIG. 6A,each of the two opposite outer sidewalls of the tibial component 1further has a second side wall 17. Or the second side wall 17 completelyor incompletely circles the outer sidewall of the tibial component 1.The second side wall 17 has a plurality of second through holes. Thedimension, disposing manner and material of the second side wall 17 isthe same or similar with those on the first side wall 33 on the outersidewall of the pad 3, so they are not repeated here.

Moreover, to easily observe the abrasion of the pad 3 after theoperation, an abrasion meter 32 may be disposed on the front portion ofthe pad 3. The abrasion meter 32 may be like ladder as shown in thefigure and it is made of metal material directly scribed on the outersidewall at the front portion of the pad 3. Or it may be a metal lineburied near the front portion of the pad 3. Therefore, the surgeon candirectly use X-ray imaging to obtain radiography showing the patient'sknee where the knee joint prosthesis K is implanted. By observing theabrasion meter 32 shown on the radiography, the degree of the pad 3being abraded by the femoral component 2 can be estimated.

In a preferable example, the top surface 11 of the tibial component 1looks like a concave surface, and the depth at the middle is deeper thanthat at the front or the rear. Thus, the pad 3 is easy to engage andassemble with the tibial component 1 by slide-in during surgery, but itis not limited thereto. Namely, in other embodiments, the pad 3 can bedirectly formed on the top surface 11 of the tibial component 1 whenmanufacturing by wrapping injection or insert injection, so it is notnecessary to engage the first engagement portion 31 of the pad 3 withthe second engagement portion 16 of the tibial component 1.Alternatively, in the factory, the pad 3 has been engaged with the topsurface 11 of the tibial component 1. Alternatively, the pad 3 and thetibial component 1 are isolated from each other, and the pad 3 isengaged with the tibial component 1 until performing surgery.

In a preferable example, as shown in FIG. 6B, the top surface 11 of thetibial component 1 can be a shallow-dish concave mentioned above, thesecond engagement portion 16 of the tibial component 1 can extend fromthe first portion 1 a and the second portion 1 b close to the front ofthe tibial component 1 to the middle section and look like a concavegroove. Only the middle section close to the first slot 15 isthrough-hole conformation so that the pad 3 is easy to assemble byslide-in along the direction along front-to-rear of the tibial component1 during surgery. The first engagement portion 31 a of the pad 3 firstlycontacts the concave groove of the second engagement portion 16 of thetibial component 1 and is thus limited. When the pad 3 continues toslide into, the first engagement portion 31 a of the pad 3 slides to andpenetrate a part of the through hole of the second engagement portion 16of the tibial component 1 so as to complete the engagement assembly ofthe pad 3 with the tibial component 1.

Besides, referring to FIG. 6A, in a preferable example, the tibialcomponent 1 can have no connection portion 1 c. Namely, the firstportion 1 a and the second portion 1 b of the tibial component 1 areindependently disposed and individually implanted into the correspondingtibial plateau during implanting.

Besides, a tibial component 1 is also provided, and it is similar to thetibial component 1 of the knee joint prosthesis K mentioned above. Thetibial component 1 includes the top surface 11, the bottom surface 12opposite to the top surface 11 and the first slot 15. The first slot 15passes through the top surface 11 and the bottom surface 12 toaccommodate the anterior cruciate ligament ACL and the posteriorcruciate ligament PCL. The tibial component 1 has at least one the firstprotrusion 13 disposed on the bottom surface 12. Each of the firstprotrusion 13 has at least one first through hole 14. Becausecomposition, variation or connection relationship to other elements ofeach detail elements of the tibial component 1 can refer to the previousembodiments, they are not repeated here.

Besides, a femoral component 2 is also provided. It is similar to thefemoral component 2 of the knee joint prosthesis K mentioned above.Similarly, the femoral component 2 is disposed corresponding to thetibial component 1. The top surface 11 of the tibial component 1 carriesthe femoral component 2. The femoral component 2 includes the secondslot 25 which is adapted to accommodate the anterior cruciate ligamentACL and the posterior cruciate ligament PCL. The femoral component 2 hasat least one second protrusion 23 disposed on the surface 21 against thetibial component 1. Each of the second protrusion 23 has at least onesecond through hole 24. Because composition, variation or connectionrelationship to other elements of each detail elements of the femoralcomponent 2 can refer to the previous embodiments, they are not repeatedhere.

Besides, another knee joint prosthesis K′ is also provided, and it issuitable to unicompartmental knee arthroplasty. Referring to FIG. 7A andFIG. 7B, they are schematic diagrams showing the assembly of the kneejoint prosthesis according to another embodiment. The knee jointprosthesis K′ includes a tibial component 1′ and a femoral component 2′.As shown in the figures, the knee joint prosthesis K′ of the embodimentis suitable to unicompartmental knee arthroplasty, so compared with thefemoral component 2 and the tibial component 1 mentioned in the previousembodiments, the tibial component 1′ and the femoral component 2′ bothonly have conformations corresponding to the femur unicondylar and thetibia unicondylar. As to the correspondence to the medial condyleportion or the lateral condyle portion, it is not limited. The personskilled in the art should understand that the knee joint prosthesis K′in the embodiment needs corresponding modification of detailconformation when applied to the medial condyle portion or the lateralcondyle portion according to the figures and the description. The tibialcomponent 1′ includes a top surface 11′ and a bottom surface 12′opposite the top surface 11′. The tibial component 1′ has at least onefirst protrusion 13′ disposed on the bottom surface 12′. In theembodiment, a plurality of the first protrusions 13′ are disposed forexample. Each of the first protrusions 13′ has at least one firstthrough hole 14′. In the embodiment, a plurality of the first throughholes 14′ are disposed for example. The femoral component 2′ roughlylooks like an arc and is disposed corresponding to the tibial component1′. The top surface 11′ of the tibial component 1′ carries the femoralcomponent 2′ (the surface 22′ of the femoral component 2′ which facesthe tibial component 1′ directly abuts the top surface 11′ of the tibialcomponent 1′, or alternatively the pad 3′ is utilized to buffer so thefemoral component 2′ is supported on the top surface 11′ of the tibialcomponent 1′ and the surface 22′ of the femoral component 2′ facing thetibial component 1′ does not directly contact the top surface 11′ of thetibial component 1′ by indirect carrying manner). The femoral component2′ is slidably disposed on the tibial component 1′. After the tibialcomponent 1′ is implanted into the tibial plateau of the patient, thefirst protrusion 13′ is inserted into the tibial plateau.

As to such the tibial component 1′ adapted for unicompartmental kneearthroplasty, it matches the structure of tibia unicondylar. Its frontportion is thicker than the front portion of the tibial component 1 fortibia bicondylar for total keen joint replacement. Therefore, althoughthe position block 41 of the auxiliary implantation device 4 can not beused, the abuting wall 434 of the wrench 43 can directly abut thethicker front portion of the tibial component 1′, the lock end 431 ofthe wrench 43 squeezes the top surface 11′ of the tibial component 1′,and similarly the rear portion of the first protrusion 13′ of the tibialcomponent 1′ abuts the patient's tibial plateau. The surgeon can takethe place of the patient's tibial plateau abutted by the firstprotrusion 13′ as the fulcrum, and the first protrusion 13′ of thetibial component 1′ can also slide into the patient's tibial plateau.

The femoral component 2′ has at least one second protrusion 23′ disposedon the surface 21′ against the tibial component 1′. In the embodiment,one second protrusion 23′ is disposed for example. The second protrusion23′ has at least one second through hole 24′. In the embodiment, aplurality of the second through holes 24′ are disposed for example.After the femoral component 2′ is implanted into the patient's knee, thesecond protrusion 23′ is inserted into the corresponding femoralcondyles.

In the embodiment, the tibial component 1′ and the femoral component 2′of the knee joint prosthesis K′ and the pad 3′ used together varycorrespondingly for applied to unicompartmental knee arthroplasty.Because composition, detail variation or connection relationship toother elements of other elements can refer to the previous embodiments,they are not repeated here.

Besides, another tibial component 1′ is also provided. It is similar tothe tibial component 1′ of the knee joint prosthesis K′. The tibialcomponent 1′ includes the top surface 11′ and the bottom surface 12′opposite the top surface 11′. The tibial component 1′ has at least onefirst protrusion 13′ disposed on the bottom surface 12′. Each of thefirst protrusion 13′ has at least one first through hole 14′. Becausecomposition, variation or connection relationship to other elements ofeach detail elements of the tibial component 1′ can refer to theprevious embodiments, they are not repeated here.

Besides, another femoral component 2′ is also provided, it is similar tothe femoral component 2′ of the knee joint prosthesis K′ mentionedabove. The femoral component 2′ is disposed corresponding to the tibialcomponent 1′, and the femoral component 2′ has at least one the secondprotrusion 23′ disposed on the surface 21′ against the tibial component1′, and each of the second protrusion 23′ has at least one secondthrough hole 24′. Because composition, variation or connectionrelationship to other elements of each detail elements of the femoralcomponent 2′ can refer to the previous embodiments, they are notrepeated here.

As mentioned above, as to the knee joint prosthesis, the tibialcomponent and the femoral component thereof, because the tibialcomponent and the femoral component respectively have at least one firstprotrusion and the second protrusion, and the first protrusion and thesecond protrusion respectively have at least one first through hole andat least one second through hole. After the tibial component and thefemoral component are respectively implanted into the tibial plateau andthe femoral condyles, the first protrusion is inserted into the tibialplateau and the second protrusion is inserted into the femoral condyles.The bone trabeculae in postoperative healing process will grow to passthrough the first through hole and the second through hole so as to fixthe tibial component and the femoral component to the implanted portion.Moreover, if the knee joint prosthesis is needed to replace in thefuture, the bone trabeculae can grow in the first through hole and thesecond through hole to fix the replaced tibial component or femoralcomponent.

In addition to the above effect of the knee joint prosthesis and thetibial component and the femoral component thereof, in one embodiment,because the tibial component and the femoral component respectively havethe first slot and the second slot disposed corresponding to each otherfor accommodating the cruciate ligament of the patient's knee, theorthopedic surgeons can adopt cruciate ligament-retaining to keep thestability of the postoperative joint and reduce the wear of the newjoint when performs total keen joint replacement.

Although the invention has been described with reference to specificembodiments, this description is not meant to be construed in a limitingsense. Various modifications of the disclosed embodiments, as well asalternative embodiments, will be apparent to persons skilled in the art.It is, therefore, contemplated that the appended claims will cover allmodifications that fall within the true scope of the invention.

What is claimed is:
 1. A knee joint prosthesis, comprising: a tibialcomponent, including a top surface, a bottom surface opposite to the topsurface and a first slot passing through the top surface and the bottomsurface for accommodating a cruciate ligament, wherein the tibialcomponent includes at least one first protrusion disposed on the bottomsurface, and the first protrusion includes a plurality of first throughholes; and a femoral component, carried by the tibial component andincluding a second slot for accommodating the cruciate ligament, whereinthe femoral component includes at least one second protrusion disposedon a surface thereof against the tibial component, and the secondprotrusion includes a plurality of second through holes.
 2. The kneejoint prosthesis of claim 1, wherein the tibial component includes atleast one sidewall and an engagement groove, and the sidewall surroundsthe first slot and the engagement groove is disposed on the sidewall. 3.The knee joint prosthesis of claim 1, wherein the first protrusionincludes a first cutting edge and a first base, the first base isdisposed between the first cutting edge and the bottom surface of thetibial component, and the first cutting edge gradually becomes thinneralong the extending direction thereof.
 4. The knee joint prosthesis ofclaim 3, wherein the tibial component includes at least one through holewhich does not overlap with the first base.
 5. The knee joint prosthesisof claim 1, wherein the tibial component includes a first side wallhaving a plurality of first apertures.
 6. The knee joint prosthesis ofclaim 1, wherein the femoral component includes at least two holdingnotches respectively located at two sides thereof.
 7. The knee jointprosthesis of claim 1, wherein the second protrusion includes a secondcutting edge and a second base, the second base is disposed between thesecond cutting edge and the surface of the femoral component away fromthe tibial component, and the second cutting edge gradually becomesthinner along the extending direction thereof.
 8. The knee jointprosthesis of claim 1, wherein the second protrusion includes at leastone position pillar which is disposed on the middle segment of thesecond protrusion.
 9. The knee joint prosthesis of claim 1, furthercomprising at least one pad located between the tibial component and thefemoral component.
 10. The knee joint prosthesis of claim 9, wherein thepad includes a second side wall having a plurality of second apertures.11. The knee joint prosthesis of claim 9, wherein the pad includes anabrasion meter.
 12. A tibial component, comprising: a top surface, abottom surface opposite to the top surface, and a slot passing throughthe top surface and the bottom surface for accommodating a cruciateligament, wherein the tibial component includes at least one protrusiondisposed on the bottom surface and the protrusion includes a pluralityof through holes.
 13. The tibial component of claim 12, wherein thetibial component includes at least one sidewall and an engagementgroove, and the sidewall surrounds the slot and the engagement groove isdisposed on the sidewall.
 14. The tibial component of claim 12, whereinthe protrusion includes a cutting edge and a base, and the base isdisposed between the cutting edge and the bottom surface of the tibialcomponent, and the cutting edge gradually becomes thinner along theextending direction thereof.
 15. The tibial component of claim 12,wherein the tibial component includes at least one through hole whichdoes not overlap with the base.
 16. The tibial component of claim 12,wherein the tibial component includes a first side wall having aplurality of first apertures.
 17. A femoral component, disposedcorresponding to a tibial component, wherein the tibial componentcarries the femoral component, the femoral component comprises: a slotfor accommodating a cruciate ligament, wherein the femoral componentincludes at least one protrusion on a surface thereof against the tibialcomponent, and the protrusion includes a plurality of through holes. 18.The femoral component of claim 17, wherein the femoral componentcomprises two holding notches respectively located at two sides thereof.19. The femoral component of claim 17, wherein the protrusion includes acutting edge and a base, the base is disposed between the cutting edgeand the surface of the femoral component away from the tibial component,and the cutting edge gradually becomes thinner along the extendingdirection thereof.
 20. The femoral component of claim 17, wherein theprotrusion includes at least one position pillar disposed on the middlesegment of the protrusion.